Method for detecting small molecule analytes using magnetoresistant sensors

ABSTRACT

Small molecule analytes (less than 1000 Daltons) in a fluid sample are detected using a competitive assay in a magnetic biosensor. The fluid sample is added to a biosensor detection chamber together with detection probes and magnetic tags which bind to the detection probes. The magnetic biosensor is functionalized with a capture probe that shares an epitope with the analytes, and the detection probe is capable of binding the epitope shared by the analytes and the capture probe, so that the presence of the analyte prevents detection probes (and magnetic tags) from binding to the biosensor. By measuring the binding of the magnetic tags to the magnetic biosensor, an amount of analytes in the solution is determined.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.15/281793 filed Sep. 30, 2016, which claims priority from U.S.Provisional Patent Application No. 62/236708 filed Nov. 2, 2015, both ofwhich are incorporated herein by reference.

FIELD OF THE INVENTION

The invention relates generally to biosensing devices and techniques.More specifically, it relates to methods of detecting small moleculeanalytes in samples using magnetic sensors.

BACKGROUND OF THE INVENTION

The need for methods to detect small molecule analytes in smallquantities has motivated the development of a variety of biosensingtechniques. For example, current high sensitivity immunoassay techniquesuse a competitive assay reaction scheme that requires washing betweensample addition and analyte detection to remove background signal andprovide required sensitivity. This washing adds additional steps andcomplexity to the technique, limiting its use. There remains a need forbiosensing techniques with very high sensitivity that are simple enoughto be suitable for point of care applications.

SUMMARY OF THE INVENTION

In one aspect, the present invention provides a technique for detectionof small molecule analytes without sacrificing sensitivity. To the bestof our knowledge, this is the first demonstration of magnetic biosensorsthat are capable of detecting small molecules (i.e., molecules less than1000 Daltons in molecular weight). A method for detecting small moleculeanalytes according to embodiments of the invention uses magnetic sensorsand nanoparticle tags. The assay involves a capture probe, which sharesan epitope with the sample analyte. The capture probe competes with thesample analyte for small molecule detection probes (such as antibodies,Fab fragments, single chain variable fragments, aptamers, or wholereceptors). This capture probe is immobilized onto the surface of asensor to capture detection probes in close proximity to the sensor. Thepresence of the analyte of interest in the sample interferes with thebinding of the detection probes to the capture probes in a concentrationdependent manner. After the detection probe binds the capture probe, thebinding of magnetic tag to the detection probe brings the magnetic taginto close proximity to the sensor, which then detects the bindingevent. The binding of detection probes to the capture probe inverselyrelates to the degree to which the detection probe has been bound bysample analyte in solution. Thus, the amount of sample analyte insolution can be calculated.

In one aspect of the invention, a method is provided for detection ofanalytes in a fluid sample using competitive assay in a magneticbiosensor. The method includes adding the fluid sample containing theanalytes, detection probes, and magnetic tags to the magnetic biosensor.The analytes being detected are small molecules, which is defined hereinto mean that they have weights less than 1000 Daltons. The magneticbiosensor is functionalized with a capture probe that shares an epitopewith the analytes, and the detection probe is capable of binding theepitope shared by the analytes and the capture probe. The method alsoincludes measuring binding of the magnetic tags to the magneticbiosensor via the detection probes and the capture probes, anddetermining an amount of analytes in the solution from the measuredbinding of the magnetic tags to the magnetic biosensor.

In some instances of the method, two or more of the fluid sample,detection probes, and magnetic tags may be mixed together prior toadding them to the magnetic biosensor. For example, the detection probesand the magnetic tags may be conjugated prior to their addition to themagnetic biosensor. In other instances of the method, the fluid sample,detection probes, and magnetic tags may be added to the magneticbiosensor sequentially.

In the present context, adding a compound to the biosensor is understoodto mean introducing it to a biosensor reaction chamber containing abiosensor element so that it can react with the biosensor element.

The magnetic biosensor preferably includes multiple magnetic biosensorelements. Some implementations include control biosensor elements thatare not functionalized with capture probes that can bind to the analytesor to the detection molecules, in which case determining the amount ofthe analytes includes comparing the measurements of binding of themagnetic tags to the magnetic biosensor with measurements from thecontrol biosensor elements. In some implementations, the magneticbiosensor elements are functionalized with different types of captureprobes that share corresponding distinct types of epitopes with multiplecorresponding distinct types of analytes, and the fluid sample containsthe multiple distinct types of analytes; the method then includes addingto the magnetic biosensor multiple distinct types of detection probesthat are capable of binding the multiple corresponding distinct types ofepitopes. The method may also include measuring binding of the magnetictags to the magnetic biosensor elements functionalized with differenttypes of capture probes, and determining amounts of the distinct typesof analytes in the solution from the measured binding of the magnetictags to the magnetic biosensor elements.

The amount of analytes in the solution may be determined from themeasured binding of the magnetic tags to the magnetic biosensor bymeasuring electrical signals from magnetic biosensor elements (e.g.,giant magnetoresistive sensors) to detect changes in electromagneticproperties of the biosensor elements due to binding of the magnetictags.

In another aspect, the invention provides a method for detection ofanalytes in a fluid sample using direct binding in a magnetic biosensor.The method includes adding the fluid sample containing the analytes andmagnetic tags to the magnetic biosensor. The analytes are smallmolecules that have weights less than 1000 Daltons. The magneticbiosensor is functionalized with a capture probe that changesconformation upon binding to the analytes, and the conformation changesenable the capture probe to bind to the magnetic tags. The method alsoincludes measuring binding of the magnetic tags bound to the captureprobes of the magnetic biosensor, and determining an amount of analytesin the solution from the measured binding of the magnetic tags to thecapture probes.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-B illustrate a biosensing technique using functionalizedmagnetic biosensors, and detector probes bound to magnetic tags,according to an embodiment of the invention.

FIG. 1C shows a portable system for implementing a biosensing techniqueaccording to an embodiment of the invention.

FIG. 1D shows detail of a disposable biosensor cartridge and a magneticbiosensor array contained in the cartridge, according to the embodimentof the invention shown in FIG. 1C.

FIG. 1E is a schematic diagram of a coil driver circuit, according tothe embodiment of the invention shown in FIG. 1C.

FIG. 1F is a magnetic biosensor array detection circuit, according tothe embodiment of the invention shown in FIG. 1C.

FIG. 1G is a schematic illustrating steps of a competitive assay usedfor magnetic biosensing of small analytes, according to an embodiment ofthe invention.

FIG. 1H is a graph of a real-time measurement of GMR biosensor signalsfor THC at 5 ng/mL in saliva, according to an embodiment of theinvention.

FIG. 2 illustrates how saliva samples can be easily collected using acotton swab, syringe, and filter unit, according to an embodiment of theinvention.

FIG. 3A is a graph of normalized measurement signal vs. concentration ofanalyte for three different concentrations of antibodies, according toan embodiment of the invention.

FIG. 3B is a graph of GMR biosensor signal vs sample incubation timesfor two different concentrations of analyte, according to an embodimentof the invention.

FIG. 3C is a graph of GMR biosensor signal vs analyte concentration,according to an embodiment of the invention.

FIG. 3D is a graph of GMR biosensor signal vs analyte concentration,according to an embodiment of the invention.

FIG. 3E is a graph of GMR biosensor signal vs analyte concentration,according to an embodiment of the invention.

FIG. 4A illustrates assembled and disassembled views of a biosensorcartridge with two reaction chambers, according to an embodiment of theinvention.

FIG. 4B is a graph of GMR biosensor signal vs analyte concentration,according to an embodiment of the invention.

FIG. 4C is a graph of GMR biosensor signal vs analyte (morphine)concentration, according to an embodiment of the invention.

FIG. 4D is a graph of GMR biosensor signal vs analyte (THC)concentration in blood, according to an embodiment of the invention.

FIG. 5 is a schematic illustration of a multiplexing magnetic biosensorarray and method for detecting multiple distinct types of smallanalytes, according to an embodiment of the invention.

FIGS. 6A-B illustrate a biosensing technique for detection of smallmolecule analytes in a fluid sample using direct binding in a magneticbiosensor, according to an embodiment of the invention.

DETAILED DESCRIPTION

A biosensing technique according to one embodiment of the invention isillustrated in FIGS. 1A-B. Magnetic biosensor elements 100 arepositioned on a substrate 104 and their surfaces are functionalized withcapture probes 106. The biosensor elements are contained in a reactionchamber 110. Detection probes 112 that bind to magnetic tags 114, and asample containing a small molecule analyte 116 are added to the chamber110. The detection probes 112 are selected to be capable of binding toboth the capture probe 106 and to the analyte 116. As a result, a lowerconcentration of the analyte results in more detection probes binding tothe capture probes on the biosensor elements, as shown in FIG. 1A. Thisyields high signal output from the magnetic sensor element 100, whosesignal depends on the magnetic tags 114 in close proximity to thesurface of the element. Conversely, a higher concentration of analytesresults in fewer detection probes binding to the capture probes on thebiosensor elements due to significant competitive inhibition of thedetection probe by the sample analyte, as shown in FIG. 1B. This yieldslower signal output from the magnetic sensor element. There is thus aninverse relationship between the amount of analyte in sample to thesignal output by a magnetic sensor in the competitive reaction scheme.In some embodiments, a biosensor element 102 is not functionalized tobind to the detection probe (i.e., either not functionalized at all, orfunctionalized such that it does not bind to the detection probe). Thesignal from element 102 can serve as a negative control sensor. Inaddition, or alternatively, elements may be functionalized to serve aspositive control sensors. For example, the positive control sensors maybe functionalized with capture probes that can directly bind to magnetictags without binding to the analyte or detection probes, so that thesesensors produce high signals.

Following the principles above, a method of detecting at least oneanalyte according to an embodiment of the invention uses the followingcompetitive assay scheme:

1) Fabricate an array of magnetic sensors and functionalize the surfacessuch that a capture probe can be bound to the sensor surface.

2) Spot the capture probe that shares an epitope with the analyte ofinterest.

3) Add sample containing the analyte of interest.

4) Add detection probe capable of binding the epitope shared by theanalyte of interest and capture probe.

5) Add magnetic tags.

6) Monitor the binding of the magnetic tags to the detection probe boundto the capture probe, and determine the amount of sample analyte in thesolution.

As an example of the technique adapted for detectingtetrahydrocannabinol (THC) analytes (314 Daltons) in a saliva sample,the biosensor elements may be giant magnetoresistive (GMR) sensorelements functionalized with bovine serum albumin (BSA) conjugated withTHC molecules. The detection probe is anti-THC bound to a magneticnanoparticle complex. Other sensor elements may be functionalized withBSA or BSA-Biotin, which serve as biological negative and positivecontrols, respectively. The technique may be implemented using a systemincluding an 10×8 array of giant magnetoresistive sensors. Salivasamples containing unknown amounts of THC are mixed with biotin labeledantibodies for THC and are added to the reaction chamber with thesensors. Binding of anti-THC antibodies to the BSA-THC coated sensors ismonitored with the addition of streptavidin labeled magneticnanoparticles. The amount of binding is concentration dependent andinversely related to the amount of THC in saliva. As more THC is addedto the saliva sample, the signal from the GMR sensor decreases.

The technique may be implemented as a hand-held point-of-care devicethat enables rapid and precise detection of small amounts of THC withoutthe need for washing. Until now, GMR biosensors have only been used tomeasure large proteins, with a focus on cancer diagnosis. Thecombination of GMR biosensor technology with a competitive immunoassayassay scheme provides surprising improvement in biosensor sensitivity,with the ability to detect low nanomolar concentrations of very smallmolecules.

For illustrative purposes, an example of such a device for implementingthe techniques of the present invention are now described in detail.

FIG. 1C shows a mobile technology system that facilitates rapid andprecise measurement of low nanomolar concentrations of THC in a 50 μlsaliva sample in a 10 to 15 minute timeframe. It includes a giantmagnetoresistive (GMR) reader 130 with a toroid core coil 132,electrical circuits 134, and Bluetooth module 136. The system alsoincludes a disposable cartridge 138 is based on a customized design ofprinted circuit board (PCB) integrated with a GMR biosensor chip 140 andreaction chamber 142. A smartphone 144 with customized app wirelesslycommunicates with the reader 130 to control it, receive data, processthe data from the biosensors, and display the results.

The disposable cartridge 138 and magnified view of the GMR biosensorchip 140 are shown in detail in FIG. 1D. The GMR biosensor chip 140 maybe wire-bonded to a customized PCB 152, and the reaction chamber 142 maybe glued on top of the chip. The chip 140 has 80 sensors arranged in a10 row by 8 column array. Each sensor, such as sensor element 150, canbe individually functionalized for multiplex assays. The last (bottom)row of the array may be used as electrical reference sensors. As anexample, capture probes (BSA or THC-BSA) were spotted on four sensors inthe middle. The scale bar is 500 μm.

The array of GMR biosensors may be fabricated on a 10×12 mm piece ofsilicon wafer. An individual GMR biosensor has a spin valve structure ofIrMn (8)/CoFe (2)/Ru (0.8)/CoFe (2)/Cu (2.3)/CoFe (4.5) (all thicknessesin nm) on seed layer, and has an active sensing area of 100×100Electrical pads are connected to the biosensors via a network grid typeof electrodes to allow external access to individual biosensors. 30 nmand 300 nm of oxide layers are deposited on the active sensing area andthe rest of the chip, respectively, to passivate the electrodes. Afterwashed with acetone, methanol, and isopropanol, the chip is glued on acustomized PCB, and wire-bonded to the electrical pads. Then, the chipis treated with 10% (3-Aminopropyl)triethoxysilane (APTES,Sigma-Aldrich, USA) in acetone for 30 min. After washing with acetoneand distilled water sequentially, a reaction chamber is installed on topof the chip to accommodate samples and reagents. THC-BSA (Fitzgerald,USA), BSA (Sigma-Aldrich, USA), and biotinylated BSA (Sigma-Aldrich,USA) are then spotted on different sensors with replicates using anon-contact arrayer (Scienion, USA). The cartridge is stored overnightin a humid chamber at 4° C. The chip is washed with rinsing buffer (PBSpH 7.4 with 0.1% BSA and 0.05% Tween-20), and blocked with 1% BSA(Sigma-Aldrich, USA) for 1 hour before use.

The measurement reader is composed of two stacked PCBs and a cartridgeintegrated with GMR biosensor chip. The two PCBs are connected via twoconnectors (16 pins and 20 pins). The top board is equipped with areceptacle for the cartridge and a toroid magnetic core coil with 470 μFceramic capacitor for LC resonance. The LC tank is driven by two poweramplifiers in a bridge-tied load configuration on the top board as shownin FIG. 1E. A coil driver circuit includes a gain controlling unit andcoil driving unit. The gain controlling unit produces two differentmagnitudes of magnetic field at the frequency of ω_(m) to operate thereader and calibrate the sensor response. The coil driving unit operatesa LC tank that incorporates a coil and ceramic capacitor using poweramplifiers. Sinusoid signals at the resonant frequency and controlsignals for the gain of the magnetic fields are transferred via the 16pin connector, and the 20 pin connector links GMR biosensors on thecartridge to the bottom board. The bottom board has analog and digitalcircuits to process the signals from GMR biosensors and to control aBluetooth module to communicate with a smartphone.

To reduce the effect by flicker noise of GMR sensor, double modulationscheme is implemented as shown in FIG. 1F. Direct digital synthesizer(DDS) generates a carrier frequency (ω_(c)) and a frequency for externalmagnetic field (ω_(m)) to employ a double modulation scheme. A carriertone subtraction circuit reduces the magnitude of the carrier tone bysubtracting signals of pre-matched resistors from sensor signals. Ananalog to digital conversion (ADC) circuit converts amplified analogsignals into 16-bit digital signals after the signals pass through ananti-aliasing filter. A micro-controller processes and transfers thedata to a smartphone via Bluetooth.

The bottom PCB provides a sinusoidal voltage to the GMR sensors whilethe magnetic field generated by the toroid core coil magneticallyexcites the GMR biosensors. The electrical current from GMR biosensorsis amplified by carrier tone subtraction circuit. Then the 20-bit ADCchip (Linear Technology, LTC2378) samples the amplified signal andtransfers the digitized signal to the microcontroller (ATSAM3X8EAAU,Atmel Corporation) for further analysis with Fast Fourier Transform.Temperature and magnetoresistive ratio (MR) correction algorithm is usedto remove changes in signal due to temperature fluctuation and variationin sensor fabrication. The microcontroller transferred the processeddata to the Bluetooth module (HC-06) on the bottom board using SerialPeripheral Interface (SPI). Then, a smartphone connected via Bluetoothreceives and displays the result on the screen using a custom app.

FIG. 1G is a schematic illustrating how the device is used to perform acompetitive assay. Step 1: anti-THC biotinylated antibodies (detectorprobes) 170 are mixed with a sample containing THC molecules 172 andpreincubated for 15 min to bind to THC.

Step 2: 50 μL of the mixture is added to the chip reaction chambercontaining a functionalized biosensor chip. The chip has bovine serumalbumin (BSA) 174 and THC-BSA 176 immobilized on different sensors 178,180, respectively. In addition, some sensors are functionalized withbiotinylated BSA (Biotin-BSA). The solution is incubated for unoccupiedantibodies 170 to bind to THC-BSA 176 on the sensors for an additional15 min.

Step 3: Unbound antibodies are washed, the disposable chip is insertedinto the measurement reader, and 40 μL of streptavidin-coated MNPs 182are then added to the chip reaction chamber, where they bind toantibodies 170. The stray field from the bound MNPs disturbs themagnetization of biosensors underneath, which changes the resistance ofthe biosensor. The changes in resistance, monitored as GMR biosensorsignals (ΔMR/MR0), are proportional to the number of bound MNPs and havean inverse relationship with the concentration of THC in the sample dueto the nature of competitive assays.

After the cartridge is inserted into the measurement reader, a customapp based on the Android operating system (Google, USA) controls themeasurement procedure. First, the app starts to measure the resistancesof the biosensors to ensure whether the cartridge is inserted correctlyand exclude defective biosensors of the chip from the measurement. Byapplying two different magnitudes of magnetic field to the sensors, theapp calibrates the individual biosensors and normalizes the signals.Then, the app asks the user to add MNPs (Miltenyi Biotec, USA) to thechip and monitors signals from biotin-BSA-coated sensors. Signals fromthe THC-BSA, BSA, and biotinylated BSA (Biotin-BSA) sensors aremonitored. The app automatically aborts the measurement if thebiotin-BSA signals remain below 100 ppm until 1 min, which is a goodindication that the user did not add the MNPs. Otherwise, the appcontinues to monitor all signals from different sensors up to 10 min.The raw data can be sent via email.

FIG. 1H is a graph of a real-time measurement of GMR biosensor signalsfor THC at 5 ng/mL in saliva. The signals are the average of 8 identicalsensor signals and referenced to the averaged signal from referencesensors. The error bars represent standard deviations of 8 identicalsensor signals.

Saliva samples can be easily collected in the field using varioustechniques. For example, a simple sample collection strategy uses acotton swab 200, syringe 202, and filter unit 204, as shown in FIG. 2.First, oral fluid is collected with a cotton swab. The cotton swab isplaced for 1 or 2 min in the mouth of an individual who is being testedto fully absorb oral fluids. The filter unit is attached to the syringe,and the saturated cotton swab is inserted into the syringe. The plungerof the syringe is depressed to squeeze the cotton swab and release thefluid, forcing it out and through the filter unit attached to thesyringe. The filter unit removes viscous mucus, food particles, andextra debris in the sample. The filtered fluid is then collected in atest tube 206.

For THC detection, values ranging from 2 to 25 ng/mL are of interest. Toachieve better sensitivity around this range, the preferredconcentration of anti-THC biotinylated antibodies is 1 μg/mL. To arriveat this value, the inventors tested three different concentrations ofantibodies (5, 1, and 0.5 μg/mL) with THC analyte concentrations at 0, 5and 20 ng/ mL, as shown in FIG. 3A. The signals at 5 and 20 ng/mL werenormalized by the signal at 0 ng/ mL for each antibody concentration forcomparison. The antibodies at 5 μg/mL showed less reduction in signalsas the concentration of THC increases compared to other antibodyconcentrations, which results in a wider dynamic range. Theconcentration of 1 μg/ mL produced a fairly linear titration curvewithin the range, while 0.5 μg/mL showed a steeper drop at 5 ng/mL ofTHC but almost the same signal as 1 μg/mL of antibodies at 20 ng/ mL ofTHC. In addition, the mass concentrations of antibodies (1 μg/mL) andTHC (5 ng/mL) correspond to 7 nM and 16 nM in molar concentration,respectively. Considering the bivalency of the antibody, the bindingcapacity is well-matched. Thus, the depletion of antibodies by THC waseffectively monitored in the competitive assays, and we therefore preferantibodies at 1 μg/mL.

To determine a preferred time frame for incubation of a sample mixturewith the chip, three different incubation times (5, 10, and 15 min) forthe chip incubation were tested with 15 min of preincubation (FIG. 3B).The antibodies at 1 μg/mL were used to detect both THC at 0 and 5 ng/mLwith 3 different chip incubation durations. A 15 min preincubation wasperformed to mix the sample with antibodies. The data point is denotedwith an asterisk if Welch's t-test shows p<0.01. The signals weresaturated for around 15 min, and the difference between signals of 0 and5 ng/mL of THC was maximized in the case of 15 min of chip incubation.Using these conditions (1 μg/mL of antibodies and 15 min/15 minincubation), we obtained a titration curve with a dynamic range from 0to 50 ng/mL of THC in saliva (FIG. 3C). The concentration of THC in thesample varied from 0 to 100 ng/mL. The biotinylated antibodies at 1μg/mL and 15 min preincubation/15 min chip incubation were used.

Furthermore, preincubation and chip-incubation times were reduced to 5and 10 min, respectively, and the GMR sensor signals were taken at 5 minafter adding MNPs instead of 10 min to carry out the entire measurementwithin 20 min. FIG. 3D shows a titration curve of 20 min assays. Thesame concentration of anti-THC biotinylated antibodies (1 μg/mL) wasused. 5 min of pre-incubation and 10 min of incubation with the chipwere performed. The signals were obtained 5 min after adding MNPs. Theresult showed no significant loss in performance. This was because thesignal levels of 10 min chip-incubation was fairly close to those of 15min incubation as shown in FIG. 3B, and the sensor signals typicallyreached their plateaus within less than 5 min after addition of MNPs asshown in FIG. 1H. Moreover, the result revealed that preincubation timewas still not a limiting factor when it was set to 5 min. Since thepreincubation is three-dimensional mixing and binding between THC andantibodies, which is much faster than binding of antibodies to THC onplanar surfaces during the chip-incubation, the preincubation could befurther reduced, compared to the chip-incubation. Without anypreincubation, THC in a wider dynamic range (0 to 200 ng/ mL) wasdetected with 5 μg/mL of antibodies within 3 min of total assay time(FIG. 3E). The mixture of the sample and antibody was immediately addedto the chip and incubated for 2 min. The concentration of the antibodieswas 5 μg/mL, and the signals were obtained 1 min after adding MNPs. Thesignals are the average of 4 identical sensors, and the error barsrepresent the standard deviations. In this case, a higher concentrationof antibodies warranted less chip-incubation time to obtain asubstantial signal of antibody binding to THC on the surface. In asimilar manner, the assay can be further tailored to adjust thesensitivity and dynamic range by changing antibody concentration andincubation time if the cutoff concentration of THC is beyond the currentrange.

The array of sensors may be split into two groups and compartmentalizedwith separate reaction chambers. One of the compartments is used tomeasure a sample with known concentrations of analytes or without any ofthem, and the other compartment is used to measure unknown sample orsample of interest. The difference in signals between the sensors withthe same capture probe in different compartments can be used todetermine the concentrations of analytes in the unknown sample or sampleof interest.

Since the binding of the antibodies to THC is a thermodynamic process,the temperature affects the assay results and there are day-to-dayvariations in measurement signals due to temperature fluctuations,chip-to-chip variations, or incubation time variations. Thus, toincrease accuracy of the assay and minimize the measurement variation, atwo-compartment cartridge 400 where two reaction chambers 402, 404 witha gasket made of polydimethylsiloxane (PDMS) are used with a GMRbiosensor chip 406 to measure both the sample of interest and areference sample simultaneously with the same chip 406 (FIG. 4A). Theuse of two compartments ensures that both samples experience the sameexperimental condition including temperature, incubation time, andbiochip fabrication. Each compartment includes 20 biosensors. Since twosamples are measured with the same chip at the same time, allmeasurement variation such as chip-to-chip variation, temperaturefluctuation, and reagent variation can be reduced or even eliminated.For demonstration, saliva samples containing 0 and 5 ng/mL of THC,respectively, were measured with the two-compartment cartridge. With themeasurement using the two-compartment cartridge, the tester can easilydetermine whether the test result is positive or negative by thedifference between the signals of two samples. For example, if it isassumed that the cutoff concentration is 5 ng/mL (reference sample) andthe sample without THC (0 ng/mL) is collected for testing, the testresult is negative, i.e., a higher signal than the reference samplemeans negative, and a signal lower than or equal to the reference ispositive. FIG. 4B is a graph of signals from 4 THC-BSA coated sensors ineach compartment. The p-value was determined using Welch's t-test.

Although the examples discussed above for illustrative purposes focus onTHC, the techniques of the present invention are not limited to THC, butare generally applicable to other small molecules. For example, thetechnique was demonstrated with morphine (285.3 Da) by replacing THCwith morphine. The sensors were coated with morphine-BSA in lieu ofTHC-BSA, and antimorphine antibodies at 0.1 μg/mL were used. The signalsfrom zero analyte, morphine at 10 and 100 ng/mL showed statisticallysignificant differences. FIG. 4C shows the measurement of morphinespiked in saliva. 90 μL of saliva contains morphine (Cerilliant, USA) atthe indicated concentration was mixed with 10 μL of biotinylatedanti-morphine antibodies (Bioss, USA) for 15 min incubation. 50 μL ofthe mixture was added to the chip where morphine conjugated with BSA(morphine-BSA, Fitzgerald, USA) is immobilized on the sensors for 15 minincubation. After washing the chip, the chip was inserted into thereader. 40 μL of MNPs were added to the chip, and the signals were taken15 min after addition of MNPs. The p-values were determined usingWelch's t-tests.

Since the competitive assays are applicable to detection of any type ofsmall molecules, the platform could be used to detect different drugssuch as heroin and cocaine in addition to THC and morphine as well as todetect therapeutic small molecule inhibitors in cancer treatments.

In some embodiments of the invention, different capture probes fordetecting different small molecules may be functionalized on differentsensors in the array of sensors to perform multiplex assays. Then, thecorresponding detection probes that can bind their target analytesspecifically are added to the biosensor. For example, with themultiplexing capability of the GMR biosensor chip, the technique can beused to simultaneously detect multiple analytes (e.g., THC—COOH and THC,or THC and its metabolites in blood and urine).

An example of a multiplexing magnetic biosensor array 500 is shown inFIG. 5. It has multiple magnetic biosensor elements grouped in fourregions 502, 504, 506, 508. The biosensor elements in each region arefunctionalized with a common type of capture probe that is differentfrom the type of capture probe in the other regions. Each type ofcapture probe shares a corresponding distinct epitope with acorresponding distinct type of analyte. In effect, it is animplementation that performs the single-analyte method in parallel in asingle sensor. A fluid sample 510 contains the multiple distinct typesof analytes 512, 514, 516, 518. Multiple distinct types of detectionprobes 520, 522, 524, 526 that are capable of binding the multiplecorresponding distinct types of epitopes are then added. The binding ofthe magnetic tags to the magnetic biosensor elements functionalized withdifferent types of capture probes is measured, and the amounts of thedistinct types of analytes in the solution is determined from themeasured binding of the magnetic tags to the magnetic biosensorelements. This multiplexing technique can also be combined with the useof positive and negative control sensor regions, as described earlier.

It will be appreciated that the principles of the invention are notlimited to the specific techniques or devices described above forillustrative purposes, but may be altered in various ways. For example,

The reaction scheme may have variations, such as:

a) The detection probe and magnetic tags may be pre-conjugated, thenadded to the sensor array after addition of sample.

b) The detection probe and magnetic tags may be pre-conjugated,pre-mixed with sample, and then added to the sensor array as one wholemixture.

c) The detection probe, magnetic tags, and sample may be simultaneouslypre-mixed prior to addition to the sensor array.

d) The detection probe, magnetic tags, or a conjugate of the two may belyophilized on or in proximity to the array of sensors.

The reagents may be delivered via microfluidics. The reagents may bedelivered via paper-based or gel-based platform to the sensor or vialateral flow method.

Mechanical stimulation such as shaking, vibrating, or stirring may beused to mix reagents.

The capture probe may be spotted on each sensor locally by surfacetension of the solution, structural confinement, chemical treatment(e.g., hydrophobic/philic treatment), or delivery via an imprintingmethod.

The magnetic sensors may be magnetic tunnel junction sensors, Halleffect sensors, or magnetoresistive sensors such as anisotropicmagnetoresistive sensors and giant magnetoresistive sensors.

The magnetic tags may be magnetic beads, magnetic nanoparticles,magnetic disks, and magnetic rods. They can bind to the detection probesvia protein-protein interactions, DNA-DNA interaction, or chemicalreactions.

An aptamer may be used instead of an antibody for the detection probe.In some cases, this could yield improved sensitivity, specificity, andprovide a more thermally stable alternative to an antibody basedapproach.

In addition, the technique is not limited to saliva, but is capable ofdetecting small analytes in blood, because GMR biosensors arematrix-insensitive. FIG. 4D shows the measurement of THC spiked inblood. A blood sample was obtained from Stanford Blood Center as blooddonation, and either zero or 5 ng/mL of THC was spiked in the bloodusing a 1:9 mixing ratio. The anti-THC biotinylated antibodies at 50ng/mL were added to the sample, and the mixture was incubated with thechip. The p-value was determined using Welch's t-test.

In another aspect, the invention provides a method for detection ofsmall molecule analytes in a fluid sample using direct binding in amagnetic biosensor, as illustrated in FIGS. 6A-B. A magnetic biosensorelement 600 is functionalized with a capture probe 602 that changesconformation upon binding to the analytes 604, as shown in FIG. 6A. Theconformation changes in the capture probe 602 when bound to the analyte604 then enable the capture probe to bind to the magnetic tags 606, asshown in FIG. 6B. The process thus includes adding a fluid samplecontaining the analytes and magnetic tags to the magnetic biosensorfunctionalized with the capture probes. The binding of the magnetic tagsbound to the capture probes of the magnetic biosensor is measured, andthe amount of analytes in the solution is determined from the measuredbinding of the magnetic tags to the capture probes. This technique canalso be used with control sensor elements, and may also be adapted formultiplexing using differently functionalized regions of a sensor array.

1. A method for detection of analytes in a fluid sample using directbinding in a magnetic biosensor, the method comprising: adding the fluidsample containing the analytes and magnetic tags to the magneticbiosensor, wherein the analytes have weights less than 1000 Daltons;wherein the magnetic biosensor is functionalized with a capture probethat changes conformation upon binding to the analytes; wherein theconformation changes enable the capture probe to bind to the magnetictags; measuring binding of the magnetic tags bound to the capture probesof the magnetic biosensor; determining an amount of analytes in thesolution from the measured binding of the magnetic tags to the captureprobes.